Treatment device for surgically correcting ametropia of an eye and method for creating control data therefore

ABSTRACT

A treatment device for the surgical correction of hyperopia in the eye comprising a laser device controlled by a control device. The laser device separating corneal tissue by applying laser radiation. The control device controls the laser device for emitting the laser radiation into the cornea such that a lenticule-shaped volume is isolated. Removal thereof effects the desired correction. The control device ( 12 ) predefines the volume such that a posterior surface and an anterior surface are connected via an edge surface that has a width in projection along the visual axis that is wider than the one which a straight line in the same projection, that is perpendicular at the edge of the posterior or the anterior surface would have relative to the associated surface and connects the anterior surface to the posterior surface or to the perceived extension thereof.

PRIORITY CLAIM

The present application is a National Phase entry of PCT Application No. PCT/EP2008/009076, filed Oct. 27, 2008, which claims priority from German Application Number 102007053283.2, filed Nov. 8, 2007, the disclosures of which are hereby incorporated by reference herein in their entirety.

FIELD OF THE INVENTION

The invention relates to a treatment apparatus for surgical correcting defective vision in the eye, the treatment apparatus having a laser device which is controlled by a control device and separates corneal tissue by applying laser radiation, the control device being adapted to control the laser device for emitting the laser radiation into the cornea in such a way that a lenticular volume is thus isolated in the cornea, the removal of which from the cornea effects the desired correction.

The invention further relates to a method for generating control data for a laser device of a treatment apparatus for operatively correcting defective vision in the eye, which laser device separates corneal tissue by applying laser radiation, wherein the control data control during operation the laser device for emitting the laser radiation into the cornea in such a way that a lenticular volume is thus isolated in the cornea, the removal of which from the cornea effects the desired correction.

Finally, the invention relates to a method for operatively correcting defective vision in the eye, corneal tissue being separated and a lenticular volume thus being isolated and removed in the cornea, the removal of which from the cornea effects the desired correction, by applying laser radiation.

BACKGROUND

The conventional way to correct defective vision of the human eye is a pair of spectacles. However, meanwhile use is also increasingly being made of refractive surgery which effects a correction of defective vision by altering the cornea of the eye. The aim of the operating methods is in this case to alter the cornea selectively in order to influence the refraction of light. Different surgical methods are known for this purpose. Most widespread at present is what is known as laser-assisted in situ keratomileusis, which is also abbreviated to LASIK. In this case, a corneal lamella is firstly detached from the surface of the cornea on one side and folded to the side. This lamella can be detached by means of a mechanical microkeratome or else by means of what is known as a laser keratome, such as is sold by Intralase Corp. Irvine, USA, for example. Once the lamella has been detached and folded to the side, the LASIK operation provides the application of an excimer laser which removes by ablation the corneal tissue exposed in this way. Once the volume positioned in the cornea has been vaporised in this way, the corneal lamella is folded back to its original site.

The application of a laser keratome to expose the lamella is advantageous, as this reduces the risk of infection and increases the quality of the cut. In particular, the lamella can be produced at a very much more constant thickness. The cut is also potentially smoother; this reduces subsequent optical disturbances caused by this interface which remains even after the operation.

When generating a cut face in the cornea by laser radiation, conventionally pulsed laser radiation is introduced into the tissue, the pulse length being generally less than 1 ps. As a result, the power density, which is necessary for triggering an optical breakthrough, for the respective pulse is confined to a small spatial area. In this regard, U.S. Pat. No. 5,984,916 clearly discloses that the spatial region of the optical breakthrough (in this case the interaction generated) highly depends on the pulse duration. A high focusing of the laser beam in combination with the aforementioned short pulses thus allows the optical breakthrough to be employed with pinpoint accuracy in the cornea. For generating the cut, a series of optical breakthroughs is generated at predetermined points in such a way that the cut surface is formed as a result. In the aforementioned laser keratome, the cut surface forms the lamella which is to be folded down before the use of the laser ablation.

In the conventional LASIK method, exposed corneal tissue is vaporised; this is also referred to as “grinding” of the cornea by means of laser radiation. The removal of volume that is necessary for correcting defective vision is in this case set for each surface element of the exposed cornea by the number of laser pulses and the energy thereof. Different amounts of material are removed in accordance with the number and energy of the laser pulses.

SUMMARY OF THE INVENTION

Very recently, the operating method mentioned initially has been described and examined in first tests. Laser radiation is used to isolate a volume in the cornea and then to remove the piece of tissue forming this volume. As pulsed laser radiation is generally used in this case too, reference is made to femtosecond lenticule extraction or FLEx for short. The volume is referred to as the lenticule.

Now, experimental values which are suitable for grinding the cornea by means of ablation laser radiation cannot be used for the FLEx method of refractive eye surgery, in which the volume to be removed from the cornea is not removed by the ablation of exposed corneal tissue, but is isolated in the cornea by a three-dimensional cut face and thus made suitable for removal, as the approaches of vaporising material to be removed, on the one hand, and removing an isolated volume, on the other hand, are too different. This applies most particularly to the selection of the cut surface bounding the volume to be removed, as there is no such cut surface in the conventional LASIK operation. The healing processes after the operation are also different, as the faces have different surface structures.

Manual removal requires a certain mechanical stability of the piece of tissue that is, in addition to the intended refractive effect, a further requirement. From this point of view, the piece of tissue should therefore be designed to be just as thick as the remaining thickness of the cornea, which is set after the removal of the piece of tissue, still allows.

This desire is opposed by the requirement for shaping allowing the refractive effects of the healing processes to be minimised or at least to be made predictable. That is to say, if the lenticules are shaped in such a way that healing processes contribute to a considerable degree to the alteration of the correction which is directly caused by the refractive therapy, for example as a result of a thickening of the cornea, then the patients would feel this to be disadvantageous. Such negative influences of healing processes are referred to as regression. It is necessary to have healing processes proceed with as little regression as possible, i.e. without refractive alterations; in other words: the refractive effect is to occur as rapidly as possible to the desired extent and then remain constant at all times. However, this is not always possible, so that the regression associated with healing processes often has to be factored into the planning of a refractive therapy. On account of physiological properties of the human eye, it is to be expected that hyperopic corrections by means of the FLEx method can generally be influenced more intensively by healing processes of this type. If these refractive changes in the course of the healing processes cannot be avoided altogether, it is therefore desirable at least to make them as slight and predictable as possible.

The prior art does not offer any assistance in this regard in corrections of hyperopia, as the previously known cut and lenticule shapes relate to corrections of myopia.

Overall, there are thus in many areas different and in some cases also new requirements in the refractive correction of defective vision by means of FLEx compared to in the conventional LASIK method.

It is therefore the object of the present invention to provide a treatment apparatus or a method of the type mentioned at the outset in such a way that the cut faces for the lenticule are advantageous both for secure removal and for the healing process.

According to the invention, this object is achieved by a treatment apparatus for surgically correcting hyperopia in an eye, the treatment apparatus having a laser device which is controlled by a control device and separates corneal tissue by applying laser radiation, the control device being adapted to control the laser device for emitting the laser radiation into the cornea in such a way that a lenticular volume is thus isolated in the cornea, the removal of which from the cornea effects the desired correction of hyperopia, wherein the control device, when controlling the laser device, defines the lenticular volume in such a way that the lenticular volume has a posterior face and an anterior face, the edges of which are connected via an edge face, wherein a cut curve made up of the edge face and a plane in which an axis of vision of the eye lies having transversely to the axis of vision a width which is greater than that which would have in the same projection plane a straight line which is perpendicular at the edge of the posterior or the anterior face on the respective face and connects the anterior face to the posterior face or to the notional continuation thereof.

This object is further achieved by a method for generating control data for a laser device of a treatment apparatus for operatively correcting hyperopia in an eye, which laser device separates corneal tissue by applying laser radiation, wherein during operation the control data control the laser device for emitting the laser radiation into the cornea in such a way that a lenticular volume is thus isolated in the cornea, the removal of which from the cornea effects the desired correction of hyperopia, wherein the control data define the lenticular volume in such a way that it has a posterior face and an anterior face, the edges of which are connected via an edge face, wherein a cut curve made up of the edge face and a plane in which an axis of vision of the eye lies having transversely to the axis of vision a width which is greater than that which would have in the same projection plane a straight line which is perpendicular at the edge of the posterior or the anterior face on the respective face and connects the anterior face to the posterior face or to the notional continuation thereof.

Finally, the object is also achieved by a method for surgically correcting hyperopia in an eye, corneal tissue being separated by applying laser radiation and a lenticular volume thus being isolated and removed from the cornea, the removal of which volume effects the desired correction of hyperopia, wherein the lenticular volume is provided with a posterior face and an anterior face, the edges of which are connected via an edge face, wherein a cut curve made up of the edge face and a plane in which an axis of vision of the eye lies having transversely to the axis of vision a width which is greater than that which would have in the same projection plane a straight line which is perpendicular at the edge of the posterior or the anterior face on the respective face and connects the anterior face to the posterior face or to the notional continuation thereof.

The invention is based on the finding that postoperative (regression) problems in the FLEX method derive from the fact that the detached and reapplied corneal lamella is disadvantageously inserted or cannot rest smoothly at the edge of the removed volume. In order to avoid regression problems of this type, the invention provides a wide edge zone, thus producing for the corneal lamella, which merges there with the posterior cut face which was produced for isolating the lenticular volume, a transition zone causing almost no regression. If this transition zone is preferably also positioned outside the optically effective region, i.e. outside the dark-adapted pupil of the eye, the risk of further undesirable side effects is further reduced. Preferably, the transition zone has a width of between 0.1 and 1 mm.

It has further been found that regressions are particularly effectively reduced if the edge face opens as perpendicularly as possible into the anterior face. A course of this type is primarily surprising as, in the case of a perpendicular opening of this type, a step leading perpendicularly away from the front face of the cornea can also be provided for the corneal lamella positioned thereabove. However, this perpendicular opening has proven unproblematic with regard to regression if the edge face has a second portion, inclined more intensively toward the axis of vision, below this perpendicular opening. As a result of this structure, the lenticular volume has an edge thickness which is preferably between 5 and 10 μm. It has been found that an edge thickness of this type is unproblematic with regard to regression, but at the same time ensures that the piece of tissue can be removed more effectively, as the edge thickness prevents with sufficient certainty particles from becoming torn off from the edge when the piece of tissue is detached. Particles of this type influence the positioning of the corneal lamella after removal of the tissue much more intensively than does the comparatively lower edge thickness of the piece of tissue and thus the short, perpendicularly opening portion of the edge face. This configuration of the invention therefore takes an edge structure which at first sight appears negative and achieves therewith as a result lower regression, i.e. better ingrowth behaviour, than an edge which is as narrow as possible which kind of edge actually would have been expected.

The second portion of the edge face, which is inclined more intensively toward the axis of vision, can be embodied in many ways. One possible example is a straight course which runs at an angle to the first portion and is positioned at an angle of from 80° to 100° relative to the direction of the axis of vision. The second portion of the edge face can then be understood to be a chamfer. However, curved courses are also possible, for example a concave course based on the point of passage of the axis of vision, i.e. a curvature of the second portion toward the axis of vision. In this case, the second portion is then designed in the form of a rounding, for example.

Within the scope of the invention, a broad range of geometries are suitable for the edge that all positively influence the regression behaviour by providing the described wide transition zone.

In an embodiment of the invention, the edge structure is combined with a dimensioning rule for the volume of the cornea that defines the radius of curvature which the cornea has after the removal of the volume. This development of the invention therefore allows not only a regression-optimised edge structure, but also an analytical calculation of the posterior and the anterior face.

The description of the curvature of the front surface of the cornea after the correction starts in this case from defective vision data which specify the refractive power B_(BR) of a pair of spectacles which are suitable for correcting defective vision and must be positioned at a distance d_(HS) before the corneal apex in order to achieve the desired correction of defective vision. The determining of these parameters is an established standard in ophthalmology and allows the use of existing measuring appliances. It goes without saying that the measurement data used in this case can also represent astigmatism defects or defects of higher aberration orders, so that the equation for describing the radius of curvature of the cornea reduced by the volume then has corresponding angle parameters (based on cylindrical coordinates) as represented in the following Equation (1) of the description of the figures.

Preference is therefore given to an embodiment of the apparatus according to the invention or the method according to the invention in which the anterior face is positioned at a constant distance d_(F) from the front surface of the cornea and the posterior face is curved and has a radius of curvature R_(L)=R_(CV)*−d_(F), wherein R_(CV)* satisfies the following equation R_(CV)*=1/((1/R_(CV))+B_(BR)/((n_(c)−1)·(1−d_(HS)·B_(BR))))+F, and R_(CV) is the radius of curvature of the cornea before removal of the volume, n_(c) is the refractive index of the material of the cornea, F is a correction factor, B_(BR) is the refractive power of a pair of spectacles suitable for correcting defective vision, and also d_(HS) is the distance at which the pair of spectacles having the refractive power B_(BR) would have to be positioned before the corneal apex in order to achieve the desired correction of defective vision by means of the pair of spectacles.

The correction factor F is a measure of the optical effect of the reduction in thickness of the cornea of the eye on the axis of vision resulting from the removal of the volume. In a simplified calculation, the factor F may be set to zero. In a more accurate calculation, F may be calculated as follows: F=(1−1/n_(c))·(d_(C)*−d_(C)), wherein d_(C) and d_(C)* respectively denote the thickness of the cornea before and after removal of the volume and the radius R_(CV)* can be calculated iteratively in that during each iteration step a change in thickness (d_(C)*−d_(C)) is concluded from the difference (R_(CV)*−R_(CV)) and the corresponding result obtained therefrom for the change in thickness is applied in the calculation of R_(CV)* in the next iteration step. The iterative calculation for F can for example be terminated if a difference which is less than a specific limit value is all that remains for F between two iteration steps.

The configuration, provided in the embodiment, of the posterior face having a curvature which relates to that of the front surface of the cornea after the removal of the volume allows a particularly simple definition of the faces bounding the volume, as the anterior face is now positioned at a constant distance below the front surface of the cornea and the optical correction is effected by the shape of the posterior face. Notable computing effort then occurs only for the definition of the posterior face part, but not for the anterior face part. Furthermore, it has also been found that an approach of this type allows at the same time a simple analytical description of the posterior face part.

The method according to the invention for preparing the control data can be carried out without human participation. In particular, it can be executed by a computer which determines the control data from proper inputs, for example from measurement data of the eye. The participation of a doctor is in no way required above all when determining the control data, as no therapeutic intervention is as yet associated with determining the control data. Such intervention does not take place until the previously determined control data are applied.

In so far as this description has described method steps, the apparatus according to the invention contains a controller which takes care of the execution of the method steps during operation of the apparatus.

BRIEF DESCRIPTION OF THE DRAWINGS

The invention will be described in greater detail hereinafter by way of example with reference to the drawings, in which:

FIG. 1 is a schematic illustration of a treatment apparatus or a treatment device for correcting defective vision;

FIG. 1 a is a schematic illustration with regard to the construction of the treatment appliance of FIG. 1;

FIG. 2 is an illustration showing the principle for introducing pulsed laser radiation into the eye in the correction of defective vision using the treatment device of FIG. 1;

FIG. 3 is a further schematic illustration of the treatment device of FIG. 1;

FIG. 4 shows in subfigures (a), (b) and (c) schematic sectional illustrations to clarify the need for correction in the human eye in the case of defective vision;

FIG. 5 is a schematic sectional illustration through the cornea of the eye illustrating a volume to be removed for correcting defective vision;

FIG. 6 is a section through the cornea of the eye after removal of the volume of FIG. 5;

FIG. 7 is a sectional illustration similar to FIG. 5;

FIG. 8 is a schematic sectional illustration through the cornea of the eye to depict the removal of the volume;

FIG. 9 a is a plan view onto the cornea of the eye to depict the cut faces generated during the correction of the defective vision;

FIG. 9 b is a sectional illustration relative to the plan view of FIG. 9 a, depicting the profile of a volume removed for the correction of hyperopia;

FIG. 10 a is an illustration similar to FIG. 9 a, but in this case for a correction of myopia;

FIG. 10 b is an illustration similar to FIG. 9 a, but again for correction of myopia;

FIG. 11 a is an illustration similar to FIG. 9 a, but with a different guidance of the cut with respect to the removal of the volume;

FIG. 11 b is a sectional illustration similar to FIG. 9 b, but for the plan view of FIG. 11 a;

FIG. 12 a is a sectional illustration similar to FIG. 9 a, but with a different type of edge cut for bounding the volume which is removed for the correction of defective vision;

FIG. 12 b is an enlarged partial view of the edge cut of FIG. 9 a; and

FIGS. 12 c and 12 d are enlarged edge cut illustrations similar to FIG. 12 b, but for different geometries of the edge face.

DETAILED DESCRIPTION

FIG. 1 shows a treatment device 1 for an ophthalmic surgical method similar to that described in EP 1159986 A1 or U.S. Pat. No. 5,549,632. The treatment device 1 effects a correction of defective vision in an eye 3 of a patient 4 by means of a treatment laser radiation 2. The defective vision may include hyperopia, myopia, presbyopia, astigmatism, mixed astigmatism (astigmatism involving hyperopia in one direction and myopia in a direction lying at right angles thereto), aspherical defects and higher-order aberrations. The treatment laser radiation 2 is applied in the described embodiment as a pulsed laser beam focused into the eye 3. The pulse duration is in this case in the femtosecond range, for example, and the laser radiation 2 acts by means of non-linear optical effects in the cornea. The laser beam has for example 50 to 800 fs-short laser pulses (preferably 100-400 fs) having a pulse repetition frequency of between 10 and 500 kHz. In the example embodiment described, the assemblies of the device 1 are controlled by an integrated control unit, although this unit can of course also be embodied in a stand-alone manner.

Before the treatment device is used, the defective vision of the eye 3 is measured using one or more measuring devices.

FIG. 1 a shows schematically the treatment device 1. In this variant, the treatment device has at least two sub-devices or modules. A laser device L emits the laser beam 2 to the eye 3. The laser device L in this case operates fully automatically, i.e. the laser device L starts, on a corresponding start signal, to shift of the laser beam 2 and generates in this manner cut faces which are constructed in a manner to be described hereinafter and isolate a volume in the cornea of the eye. The laser device L receives beforehand via control lines which will not be designated in greater detail from a planning device P control data required for operation as a set of control data. The transmission takes place before operation of the laser device L. It is of course also possible to communicate wirelessly. As an alternative to direct communication, it is also possible to arrange the planning unit P spatially separated from the laser unit L and to provide a corresponding data transmission channel.

For example, the set of control data is transmitted to the treatment device 1 and, also preferably, an operation of the laser device L is blocked until a valid set of control data is present on the laser device L. A valid set of control data may be a set of control data which is in principle suitable for use with the laser device L of the treatment device 1. In addition, validity can also be linked to further tests being passed, for example whether particulars, which are additionally filed in the set of control data, about the treatment device 1, for example a device serial number, or about the patient, for example a patient identification number, correspond to other particulars which were for example read out from the treatment device or separately input as soon as the patient is in the correct position for operation of the laser device L.

The planning unit P generates the set of control data, which is provided to the laser unit L for executing the surgical operation, from measurement data and defective vision data which were acquired for the eye to be treated. They are supplied to the planning unit P via an interface S and originate in the illustrated example embodiment from a measuring device M which previously measured the eye of the patient 4. Of course, the measuring device M can transmit the corresponding measurement and defective vision data to the planning unit P in any desired manner.

The data can be transmitted by means of memory chips (for example by a USB or memory stick), magnetic memories (for example floppy disks), by radio (for example WLAN, UMTS, Bluetooth) or in a hard wired manner (for example USB, FireWire, RS232, CAN Bus, Ethernet, etc.). Of course, the same applies with regard to the transmission of data between the planning unit P and laser device L.

A direct radio or wired connection of the measuring device M to the treatment device 1 with regard to the transmission of data, which can be used in a variant, has the advantage that the use of false measurement and defective vision data is ruled out with maximum possible certainty. This applies in particular when the patient is transferred from the measuring device M or measuring devices to the laser device L by means of a bed device (not shown in the figure) which interacts with the measuring device M or the laser device L in such a way that the respective devices detect whether the patient 4 is in the proper position for measuring or introducing the laser radiation 2. In this case, the measurement and defective vision data can be transmitted to the treatment apparatus 1 at the same time as the patient 4 is transferred from the measuring device M to the laser device L.

Suitable means can ensure that the planning unit P always generates the set of control data pertaining to the patient 4 and the risk of an erroneous use of an incorrect set of control data for a patient 4 is all but ruled out.

The effect of the laser beam 2 is indicated schematically in FIG. 2. The treatment laser beam 2 is focused into the cornea 5 of the eye 6 by means of optics which are not be designated. This produces in the cornea 5 a focus which covers a spot 6 and in which the laser radiation energy density is so high that a non-linear effect occurs in the eye in combination with the pulse length. For example, each pulse of the pulsed laser radiation 2 can generate at the respective spot 6 an optical breakthrough in the cornea 5 of the eye, which breakthrough in turn initiates a plasma bubble indicated schematically in FIG. 2. As a result, tissue is separated in the cornea 5 by this laser pulse. When a plasma bubble is produced, the tissue layer separation comprises a larger area than the spot 6 which the focus of the laser radiation 2 covers, although the conditions for generating the breakthrough are achieved only in the focus. In order for an optical breakthrough to be generated by each laser pulse, the energy density, i.e. the fluence of the laser radiation, must be above a certain, pulse length-dependent threshold value. This relationship is known to the person skilled in the art from DE 69500997 T2, for example.

Alternatively, a tissue-separating effect of the pulsed laser radiation can also be generated in that a plurality of laser radiation pulses are emitted in a region, the spots 6 overlapping for a plurality of laser radiation pulses. A plurality of laser radiation pulses then co-operate to achieve a tissue-separating effect.

However, the type of tissue separation which the treatment device 1 uses is not relevant for the following description; all that matters is that treatment laser radiation 2 pulsed is used. For example, use may be made of a treatment device 1 such as is described in WO 2004/032810 A2. It is also essential that a large number of laser pulse foci form a cut face in the tissue, the shape of which is dependent on the pattern in which the laser pulse foci are/become arranged in the tissue. The pattern predefines target points for the position of the focus, at which points one or more laser pulse(s) is/are emitted, and defines the shape and position of the cut face. The pattern of the target points is important for the methods and apparatuses described on hereinafter and the pattern will be described in greater detail below.

In order now to execute a correction of defective vision, material is removed from an area within the cornea 5 by means of the pulsed laser radiation by separating there layers of tissue which isolate the material and then allow the material to be removed. The removal of material effects a change in volume in the cornea resulting in a change in the optical imaging effect of the cornea 5, the dimensions of which are precisely such that the previously determined defective vision is/becomes thereby corrected as far as possible. For isolating the volume to be removed, the focus of the laser radiation 2 is directed toward target points in the cornea 5, generally in a region positioned below the epithelium and the Bowman's membrane and also above the Descemet's membrane and the endothelium. For this purpose, the treatment device has a mechanism for shifting the position of the focus of the laser radiation 2 in the cornea 5. This is shown schematically in FIG. 3.

Elements of the treatment device 1 are included in FIG. 3 only in so far as they are required to understand the shifting of the focus. The laser radiation 2 is, as mentioned hereinbefore, focused to a focus 7 in the cornea 5, and the position of the focus 7 in the cornea is shifted, so that for generating the cut face at various points focussed energy from laser radiation pulses is introduced into the tissue of the cornea 5. The laser radiation 2 is provided as pulsed radiation by a laser 8. An xy scanner 9, which is embodied in a variant by two galvanometer mirrors deflecting about substantially orthogonally axes, two-dimensionally deflects the laser beam coming from the laser 8, so that after the xy scanner 9 a deflected laser beam 10 is present. The xy scanner 9 thus effects a shifting of the position of the focus 7 substantially perpendicularly to the main direction of incidence of the laser radiation 2 into the cornea 5. In addition to the xy scanner 9, a z scanner 11, which is embodied as an adjustable telescope for example, is provided for adjusting the depth position. The z scanner 11 provides for the z position of the focus 7, i.e. the position thereof on the optical axis of incidence, being shifted. The z scanner 11 can be arranged downstream or upstream of the xy scanner 9. The coordinates denoted hereinafter by x, y, z therefore relate to the shifting of the position of the focus 7.

The allocation of the individual coordinates to the spatial directions is not essential for the functioning principle of the treatment appliance 1; however, for the sake of simplicity of description, z denotes hereinafter in all cases the coordinates along the optical axis of incidence of the laser radiation 2, and x and also y denote two mutually orthogonal coordinates in a plane perpendicular to the direction of incidence of the laser beam. The person skilled in the art is of course aware that the position of the focus 7 in the cornea 5 can also be three-dimensionally described in other coordinate systems; in particular, the coordinate system does not have to be a system of rectangular coordinates. The fact that the xy scanner 9 deflects about axes at right angles to one another is therefore not compulsory; on the contrary, use may be made of any scanner which is able to adjust the focus 7 in a plane in which the axis of incidence of the optical radiation does not lie. Systems of oblique coordinates are thus also possible.

Furthermore, systems of non-rectilinear coordinates can also be used to describe or control the position of the focus 7, as will also be commented on hereinafter in greater detail. Examples of coordinate systems of this type are spherical coordinates and also cylindrical coordinates.

For controlling the position of the focus 7, the xy scanner 9 and also the z scanner 11, which jointly form a specific example of a three-dimensional focus shifting device, are activated by a controller 12 via lines which are not designated. The same applies to the laser 8. The controller 3 ensures a suitably synchronous operation of the laser 8 and also of the three-dimensional focus shifting device, implemented in exemplary fashion by the xy scanner 9 and also the z scanner 11, so that the position of the focus 7 in the cornea 5 is shifted in such a way that ultimately a material of specific volume is isolated, the subsequent removal of volume effecting a desired correction of defective vision.

The controller 12 operates in accordance with predefined control data which define the target points for the focus shifting. The control data are generally summarised in a set of control data. In one embodiment, the set of control data defines the coordinates of the target points as a pattern, wherein the sequence of the target points in the set of control data defines the sequential arrangement of the focus positions and thus ultimately a path curve (referred to in the present document also as a path for short). In one embodiment, the set of control data contains the target points as specific setting values for the focus position shifting mechanism, for example for the xy scanner 9 and the z scanner 11. For preparing the ophthalmic surgical method, i.e. before the actual surgical method is executed, the target points and preferably also the order thereof are determined in the pattern. The surgical intervention must be preplanned in such a way that the control data for the treatment device 1 are defined, the application of which data then achieves a correction of defective vision that is optimal for the patient 4.

The first step is to define the volume which is to be isolated from the cornea 5 and subsequently to be removed. As previously described with reference to FIG. 1 a, this requires the need for correction to be ascertained. FIG. 4 shows in subfigures a), b) and c) the optical conditions in the eye 3 of the patient 4. Without defective vision correction, the situation is that shown in subfigure a). The cornea 5 effects together with the lens 13 of the eye a focusing of an object lying at infinity into a focus F positioned on the z axis after the retina 14. The imaging effect derives in this case on the one hand from the lens 13 of the eye, which lens is relaxed when the eye is not accommodated, and also on the other hand from the cornea 5 of the eye that is defined substantially by a front face 15 of the cornea and also a back 16 of the cornea and likewise has an imaging effect on account of its curvature. The optical effect of the cornea 5 is caused by the radius of curvature R_(CV) of the front surface of the cornea. Subfigure a) represents the defective vision merely in exemplary fashion; in reality, the above-mentioned more complex defective visions may be present. However, the following description applies to them too, although some of the specified equations may then contain an additional angle dependency even if reference is not expressly made thereto.

For correcting defective vision, a front lens 17 in the form of a pair of spectacles is placed in a known manner, as illustrated in subfigure b) of FIG. 4, before the eye 3 at a distance d_(HS) from the vertex of the cornea 5. The refractive power B_(BR) of the lens 17 is adapted such that the lens shifts the far point of the system as a whole, i.e. the system made up of the pair of spectacles and eye, from the focus point F to the corrected focus point F* which is positioned on the retina 14.

With regard to the nomenclature used in this description, it should be noted that the addition of an asterisk to variables indicates that they are variables obtained after a correction. The focus F* is therefore that focus which is present after the optical correction which is achieved in subfigure b) of FIG. 4 by the lens 17 of the pair of spectacles.

Under the justified assumption that a change in thickness of the cornea 5 mainly modifies the radius of curvature of the air-facing anterior surface 15 of the cornea, but not the radius of curvature of the posterior surface 16 of the cornea facing the interior of the eye, the radius of curvature R_(CV) of the anterior surface 15 of the cornea is modified by the removal of the volume. The cornea 5 reduced by the volume has an imaging effect which is altered in such a way that the focus F*, which is then corrected, lies on the retina 14. After the correction an altered anterior surface 15* of the cornea is present, and a correction of defective vision is achieved even without a pair of spectacles.

The curvature to be achieved of the modified anterior surface 15* of the cornea is therefore determined for defining the pattern of the target points. In this case, the starting point is the refractive power of the lens 17 of the pair of spectacles, as determining the corresponding parameters is a standard method in ophthalmic optics. The following formula applies to the refractive power B_(BR)(φ) of the lens 17 of the pair of spectacles: B _(BR)(φ)=Sph+Cyl·sin²(φ−θ)  (1)

In this equation Sph and Cyl denote the correction values to be implemented of spherical and astigmatic refractive defects respectively and θ denotes the position of the cylinder axis of the cylindrical (astigmatic) defective vision, such as they are known to the person skilled in the art in optometry. Finally, the parameter φ refers to a system of cylindrical coordinates of the eye and is counted anticlockwise looking onto the eye, such as is conventional in ophthalmic optics. Now, with the value B_(BR), the curvature of the modified anterior surface 15* of the cornea is set as follows: R _(CV)*=1/(((1/R _(CV))+B _(BR)/((n _(c)−1)·(1−d _(HS) ·B _(BR))))+F  (2)

In Equation (2) n_(c) denotes the refractive index of the material of the cornea. The respective value is usually 1.376; d_(HS) denotes the distance at which a pair of spectacles having the refractive power B_(BR) must be positioned from the corneal apex in order to generate the desired correction of defective vision by means of the pair of spectacles; B_(BR) denotes the aforementioned refractive power of the pair of spectacles according to Equation (1). The indication for the refractive power B_(BR) can also include defective visions extending beyond a normal spherical or cylindrical correction. B_(BR) (and thus automatically also R_(CV)*) then have additional coordinate dependencies.

The correction factor F takes account of the optical effect of the change in thickness of the cornea and may be regarded in the first approximation as a constant factor. For a high-precision correction, the factor can be calculated in accordance with the following equation: F=(1−1/n _(c))·(d _(C) *−d _(C))  (3)

d_(C) and d_(C)* are in this case the thickness of the cornea before and after the optical correction respectively. For precise determination, R_(CV)* is calculated iteratively in that in the i^(th) calculation the variable (d_(C)*−d_(C)) is concluded from the difference (R_(CV)*−R_(CV)) and the corresponding result obtained therefrom for the change in thickness is applied in the (i+1)^(th) calculation. This can be carried out until a termination criterion is met, for example if the difference of the result for the change in thickness is in two successive iterations steps below a correspondingly defined limit. This limit can be defined via a constant difference, for example, corresponding to a precision of the refractive correction that is appropriate for the treatment.

If the change in thickness of the cornea of the eye is disregarded (as is entirely permissible for a simplified method), the correction value F in Equation (2) can be set to zero for a simplified calculation, i.e. disregarded and omitted. Surprisingly, the following simple equation is obtained for the refractive power of the modified cornea 5*: B _(CV) *=B _(CV) +B _(BR)/(1−B _(BR) ·d _(HS))

This equation provides the person skilled in the art in a simple manner, by means of the equation B_(CV)*=(n−1)/R_(CV)*, with the radius R_(CV)* of the anterior surface 15* of the cornea that must be present after the modification in order to obtain the desired correction of defective vision, as follows: R_(CV)*=1/((1/R_(CV))+B_(BR)/((n_(c)−1)·(1−d_(HS)·B_(BR)))).

For the volume, the removal of which effects the foregoing change in curvature of the anterior surface 15 of the cornea, the border face isolating the volume is now defined. In this regard, account must preferably be taken of the fact that the diameter of the region to be corrected, and thus the diameter of the volume to be removed, should if possible extend over the size of the pupil of the dark-adapted eye.

In a first variant, numerical methods known to the person skilled in the art are used to define a free face circumscribing a volume, removal of which effects the change in curvature. For this purpose, the change in thickness required for the desired modification of curvature is determined along the z axis. This provides the volume as a function of r, φ (in cylindrical coordinates) and this in turn provides the border face thereof.

A simple analytical calculation leads to the following second variant in which the border face of the volume is constructed by two face parts: an anterior face part facing the surface 15 of the cornea and an opposing posterior face part. FIG. 5 shows the corresponding conditions. The volume 18 is bounded towards the anterior surface 15 of the cornea by an anterior cut face 19 positioned at a constant distance d_(F) below the anterior surface 15 of the cornea. This anterior cut face 19 is also referred to, by analogy with a laser keratome, as a flap face 19, as it serves to allow in the cornea 5 of the eye a lamella in the form of a flap to be lifted, in combination with an opening cut toward the edge, from the underlying cornea 5. This type of removal of the previously isolated volume 18 is of course also possible here.

The anterior cut face 19 has a course of curvature which is positioned by d_(F) below the anterior surface 15 of the cornea. If the anterior surface is spherical during the surgery, a radius of curvature which is less than the radius of curvature R_(CV) by d_(F) can be specified for the flap face 19. As will be described hereinafter for preferred variants, a contact glass can ensure when generating the cut face 19 that the anterior surface 15 of the cornea is spherical at the moment when the cut face is generated, so that the pattern of the target points generates a spherical cut face. Although the relaxation of the eye 3 after the detachment of the contact glass may then lead to a non-spherical cut face 19, it is still at a constant distance from the anterior surface 15 or 15* of the cornea.

Posteriorly, the volume 18 which is to be removed from the cornea 5 is bounded by a posterior cut face 20 which is generally not at a constant distance from the anterior surface 15 of the cornea. The posterior cut face 20 will therefore be embodied in such a way that the volume 18 has the form of a lenticule, for which reason the posterior cut face 20 is also referred to as the lenticule face 20. In FIG. 5 the posterior cut face is illustrated, by way of example for a correction of myopia, as a likewise spherical face having a radius of curvature R_(L), wherein the centre of this curvature generally does not coincide with the centre of curvature of the anterior surface 15 of the cornea, which is likewise spherical in FIG. 5. In a correction of hyperopia, R_(L) is greater than R_(CV)−d_(F).

FIG. 6 shows the conditions after removal of the volume 18. The radius of the modified anterior surface 15* of the cornea is now R_(CV)* and can be calculated in accordance with the equations described hereinbefore, for example. The central thickness d_(L) of the removed volume 18 is in this case decisive for the change in radius, as FIG. 7 illustrates. In this figure the height h_(F) of the spherical cap defined by the anterior cut face 19, the height h_(L) of the spherical cap defined by the posterior cut face 20, and also the thickness d_(L) of the volume 18 to be removed are also indicated as further variables.

The posterior cut face 20 defines, on account of the constant distance between the anterior surface 15 of the cornea and the anterior cut face 19, the course of curvature of the anterior surface 15* of the cornea after removal of the volume 18. Thus, the posterior cut face 20 will have an angle-dependent radius of curvature, for example in a correction of defective vision taking into account cylindrical parameters. For the lenticule face 20 shown in FIG. 7, the following generally applies: R _(L)(φ)=R _(CV)*(φ)−d _(F), or in cylindrical coordinates (z, r, φ) z _(L)(r,φ)=R _(L)(φ)−(R _(L) ²(φ)−r ²)^(1/2) +d _(L) +d _(F).

When not taking account of an astigmatism, the dependency on φ is dispensed with and the lenticule face 20 is spherical. However, starting from the need for a cylindrical correction of defective vision, the lenticule face 20 generally has different radii of curvature on various axes, the radii of curvature mostly having the same vertex of course.

Furthermore, this automatically makes it clear that, in the case of a myopic cylindrical correction, the theoretical line of intersection between the flap face 19 and lenticule face 20 does not lie in one plane, i.e. at constant z coordinates. The smallest radius of curvature of the lenticule face 20 is at φ=θ+π/2; the largest is of course on the axis θ of cylindrical defective vision, i.e. at φ=θ. Unlike in the illustration of FIG. 7, in a correction of defective vision, the vertices of the flap face 19 and lenticule face 20 theoretically coincide and the lenticule face 20 is curved more intensively than the flap face 19. The thickness d_(L) of the lenticule is obtained as the central lenticule thickness in myopia.

In the case of the correction of myopia, the volume 18, which is to be regarded as a lenticule, theoretically has a line of intersection of the lenticule face 20 and flap face 19 at the edge. In the correction of hyperopia, a finite edge thickness is always provided, as the lenticule face 20 is curved less intensively than the flap face 19. However, in this case, the central lenticule density is theoretically equal to zero.

In addition to the flap face 20 and the lenticule face 19, an additional edge face is provided that bounds the bounded volume 18 of the flap face 20 and the lenticule face 19 at the edge. The cutting of this edge face is also executed using the pulsed laser beam. The structure of the edge face will be described hereinafter with reference to FIGS. 12 a-c.

The embodiment shown in the figures of the volume 18 as being bounded by an anterior cut face 19 at a constant distance from the front face 15 of the cornea and also a posterior cut face 20 is just one option for bounding the volume 18. However, it has the advantage that the optical correction is defined substantially by just one face (the lenticule face 20), so that the analytical description of the other face part of the border face is simpler.

Furthermore, optimum safety margins are provided with regard to the distance of the volume from the anterior surface 15 of the cornea and the posterior surface 16 of the cornea. The remaining thickness d_(F) between the anterior cut face 19 and the anterior surface 15 of the cornea can be set to a constant value of from 50 to 200 μm, for example. In particular, it can be selected in such a way that the pain-sensitive epithelium remains in the lamella formed by the flap face 19 below the anterior surface 15 of the cornea. The formation of the spherical flap face 19 is also in line with previous keratometer cuts; this is advantageous for the acceptance of the method.

After generating the cut faces 19 and 20, the volume 18 thus isolated is then removed from the cornea 5. This is schematically represented in FIG. 8 which further shows that the cut faces 19 and 20 are generated under the action of the treatment laser beam incident in a focus cone 21, for example by sequential arrangement of plasma bubbles, so that in a preferred embodiment the flap cut face 19 and the lenticule cut face 20 are generated by suitable three-dimensional shifting the focus position of the pulsed laser radiation 2.

However, alternatively, in a simplified embodiment it is possible for merely the flap face 19 to be formed by target points defining the curved cut face 19 at a constant distance from the anterior surface 15 of the cornea by means of pulsed laser radiation and for the volume 18 to be removed by laser ablation, for example using an excimer laser beam. For this purpose, the lenticule face 20 can be defined as a border face of the removal, although this is not mandatory. The treatment device 1 then works like a known laser keratome; nevertheless, the cut face 19 is generated on a curved cornea. The features described hereinbefore and hereinafter respectively are also possible in such variants, in particular as far as the determination of the boundary face, its geometric definition and the determination of control parameters is concerned.

If both the lenticule face 20 and the flap face 19 are generated by means of pulsed laser radiation, it is expedient to form the lenticule face 20 before the flap face 19, as the optical result in the lenticule face 20 is better (or even may be achieved only) if no alteration of the cornea 5 has yet occurred above the lenticule face 20.

The removal of the volume 18 isolated by the pulsed laser radiation can be achieved, as indicated in FIG. 8, by an edge cut 22 allowing the volume 18 to be extracted in the direction of an arrow 23 shown in FIG. 8. However, alternatively, the edge cut 22 can be embodied in such a way that it connects the anterior cut face 19, i.e. the flap face 19, in the form of a ring to the anterior surface 15 of the cornea, although the edge cut does not extend all the way round an angle of 360°. The lamella isolated in this way remains connected to the remaining tissue of the cornea 5 in a narrow region. This connecting bridge then serves as a hinge, so as to be able to fold the otherwise isolated lamella away from the cornea 5 and to detach the already isolated volume 18 made accessible in this manner from the remainder of the cornea 5 of the eye. The position of the connecting bridge can be predefined when generating the control data or the target points respectively. From this point of view, the described procedure or device therefore isolates the volume 19 within the cornea 5 and generates a lamella, connected to the remainder of the cornea of the eye via a tissue bridge, as a lid over the volume. The lid can be folded away and the volume 18 can be removed.

To generate the cut faces 19 and 20, the target points can now be arranged in a broad range of ways. The prior art, for example WO 2005/011546, describes how special spirals, which extend for example in the manner of a helical line about a main axis lying substantially perpendicularly to the optical axis (z axis), can be used to generate cut faces in the cornea of the eye. The use of a scanning pattern, which arranges the target points in lines, is also known (cf. WO 2005/011545). It goes without saying that these options can be used to generate the above-defined cut faces.

The edge face mentioned hereinbefore may be seen in greater detail in FIGS. 9 a and 9 b. Elements which have already been described with reference to other figures are provided in these figures with the same reference numerals, so that they will not necessarily be described again.

FIG. 9 a is a plan view onto the anterior surface 15 of the cornea with the flap face 19 and also the lenticule face 20 (the rim of which is indicated by a dashed line) and also the edge cut 22 in the case of a correction of hyperopia. A zone of transition between the edge of the lenticule face 20 and the flap face 19, which is achieved by an edge face 24, may also be seen in FIG. 9 a. This edge face 24 may clearly be seen in FIG. 9 b which is a sectional illustration through the illustration of FIG. 9 a along the lines A-A.

The edge face 24 effects the transition from the lenticule face 20 to the flap face 19. In this case, it is designed in the embodiment of FIG. 9 b as a conical face which is positioned more obliquely than a conical (in the plan view onto FIG. 9 a) face, which is oriented perpendicularly to the front face 15 of the cornea or to the flap face 19 extending parallel thereto, would be positioned. The edge cut 22 is positioned at an angle α to the axis of vision OA, which angle results in such perpendicular course relative to the front face of the cornea.

On the other hand, the edge face 24 extends in a more inclined manner, so that the width B, which the edge face 24 has when viewed from above and along in the direction of the optical axis OA, is greater than in the edge cut 22, for example. The corresponding angle β is accordingly also larger than the angle α.

FIGS. 10 a and 10 b show the corresponding conditions in the case of a myopic lenticule, i.e. in the correction of myopia. In this case too, the edge face 24 is provided for and leads to a finite edge thickness of the lenticule 18 that would not be provided in itself on account of the larger curvature of the lenticule face 20 compared to the flap face 10, as both faces would have, at least in their continuation, a line of intersection, i.e. the edge would end in a line of intersection.

The minimum thickness of the lenticule 18, which is present, in a hyperopic form according to FIG. 9 b, on or close to the optical axis OA, occurs therefore in a myopic lenticule according to FIG. 10 b at the edge. Accordingly, the minimum thickness d_(M) is also shown at the edge in FIG. 10 b.

It goes without saying that the sectional illustrations of FIGS. 9 b and 10 b are descriptive for the lenticule as a whole only when no higher-order correction, in particular no astigmatism, is present. If there is astigmatism, the lenticule face 20 is corrected accordingly so as to differ from sphericity; this also has an effect on the edge face 24 in a manner which is obvious to the person skilled in the art.

Finally, FIGS. 11 a and 11 b show conditions corresponding to those of FIGS. 9 a and 9 b; however, in this case, the edge cut 22, which is generated to expose the lenticule 18, extends over a very much larger angular range than in FIGS. 9 and 10.

FIGS. 9 to 11 show an edge face 24 which is designed as an oblique cut. However, the edge face 24 can also have a structure differing from such a course which is linear viewed in cross section. This is shown by way of example in FIGS. 12 a to d. In these figures, FIG. 12 a represents a sectional illustration similar to that of FIG. 9 b, 10 b or 11 b. FIGS. 12 b to 12 d are enlarged views of the detail indicated by a dotted line in FIG. 12 a and represent different options for the structure of the edge face 24.

According to FIG. 12 b the edge face 24 consists of two portions 25 and 26 which are substantially linear in cross section. The first portion 25 runs perpendicularly into the flap face 19. The height of the first portion 25 effects a thickness d_(R) of the edge. This thickness is preferably selected so as to be in the range of from 5 to 10 μm and ensures that fragments do not become torn off in the region of the edge face 24 when the lenticule 18 is removed. Such fragments would have very disadvantageous effects on ingrowth and would lead to undesirable regression. In order to achieve, despite the first portion 25 lying perpendicularly to the flap face 19, a smooth positioning of the corneal lamella 27 isolated by the flap cut 19 when the lenticular volume was removed, the second portion 26 of the edge face 24 has in the embodiment of FIG. 12 b an oblique course towards the axis of vision. This oblique course provides, in turn, a width B which is much greater than that which would be provided in an edge 24 extending perpendicularly to the flap face 19 throughout.

FIG. 12 c shows a modification of the structure of the edge face 24 of FIG. 12 b, in which a continuously curved second portion 26, which rounds off the edge between the lenticule face 20 and the flap face 19 in the region remote from the anterior surface 15 of the cornea of the eye, is formed on the first portion 25 running perpendicularly into the flap face 19. The perpendicular running-in of the first portion 25 ensures, again, a minimum edge thickness d_(R) which prevents pieces of tissue from becoming torn off from the edge of the lenticule when the lenticular tissue is removed.

This is also achieved in the edge structure according to FIG. 12 d, which is embodied in an S-shaped manner, the first portion 25 running, again, perpendicularly into the flap face 19. On account of the S-shaped structure, the sectional illustration of the edge face 24 has in this configuration a turning point, and the second portion 26 preferably ends likewise at right angles in the lenticule face 20.

The contact glass has the further advantage that the anterior surface 15 of the cornea is also automatically spherical as a result of the pressing onto the spherical underside 26 of the contact glass. Thus, when the contact glass is pressed on, the anterior cut face 19, which is positioned at a constant distance below the anterior surface 15 of the cornea, is also spherical, leading to a greatly simplified control. It is therefore preferable, quite independently of other features, to use a contact glass having a spherical contact glass underside and to bound the volume by an anterior cut face 19 and also a posterior cut face, the anterior cut face being generated as a spherical face at a constant distance d_(F) below the anterior surface 15 of the cornea. The posterior cut face has a course of curvature corresponding, apart from the distance d_(F) from the anterior surface of the cornea, to that desired for the correction of defective vision when the eye is relaxed, i.e. after the contact glass has been detached. The same applies to the definition of the target points and to the operating method respectively. 

The invention claimed is:
 1. A treatment apparatus for surgical correction of hyperopia in an eye, the treatment apparatus comprising: a laser device including a laser and scanners, the scanners each comprising mirrors, optics or a combination of mirrors and optics, which is controlled by a control device and which separates corneal tissue by applying laser radiation; the control device being programmed with an algorithm that controls the laser device including the laser and the scanners to emit the laser radiation into the cornea at a focus positioned by operation of the laser and the scanners wherein a lenticular volume is isolated in the cornea, the lenticular volume being structured such that removal of the lenticular volume effects a desired correction of hyperopia; the control device being programmed with an algorithm that controls the laser and the scanners to define the lenticular volume to have a posterior face and an anterior face and edges that are connected via an annular edge face, the edge face having, in projection along an optical axis of the eye, a first ring width that is greater than a second ring width that would be created in the projection along the optical axis of the eye by a straight line extending perpendicularly from an edge of the posterior or the anterior face to the other of the posterior or the anterior face or to an imaginary continuation of the posterior face or the anterior face.
 2. The treatment apparatus according to claim 1, wherein the control device further is programmed with an algorithm that controls the laser device such that the anterior face is positioned at a constant distance d_(F) from the anterior surface of the cornea and the posterior face is curved and has a radius of curvature R_(L)=R_(CV)*−d_(F), wherein R_(CV)* satisfies the following equation R _(CV)*=1((1/R _(CV))+B _(BR)/((n _(c)−1)·(1−d _(HS) ·B _(BR))))+F, and R_(CV) is a radius of curvature of the cornea before removal of the lenticular volume, n_(c) is a refractive index of a material of the cornea, F is a correction factor, B_(BR) is a refractive power of a pair of spectacles suitable for correcting defective vision, and also d_(HS) is a distance at which the pair of spectacles having the refractive power B_(BR) would have to be positioned before a corneal apex in order to achieve a desired correction of defective vision by the pair of spectacles.
 3. The apparatus according to claim 2, wherein the control device further controls the laser device such that the following applies F=(1−1/n _(c))·(d _(C) *−d _(C)), wherein d_(C) and d_(C)* respectively denote a thickness of the cornea before and after removal of the lenticular volume and the radius R_(CV)* can be calculated iteratively in that during each iteration step a change in thickness (d_(C)*−d_(C)) is concluded from the difference (R_(CV)*−R_(CV)) and the corresponding result obtained therefrom for the change in thickness is applied in the calculation of R_(CV)* in a next iteration step.
 4. The apparatus according to claim 1, wherein the control device further is programmed with an algorithm that controls the laser device such that the edge face has a first portion.
 5. The apparatus according to claim 4, wherein the control device further is programmed with an algorithm that controls the laser device such that the first portion opening perpendicularly into the anterior face has a height d_(R) of more than 5 μm.
 6. The apparatus according to claim 4, wherein the control device further is programmed with an algorithm that controls the laser device such that the first portion opening perpendicularly into the anterior face has a height d_(R) of at least 10 μM.
 7. The apparatus according to claim 4, wherein the control device further is programmed with an algorithm that controls the laser device such that the second portion is positioned at an angle of from 80° to 100° relative to the direction of the axis of vision.
 8. A method of generating control data for surgical correction of hyperopia in an eye, the method comprising: providing a laser device including a laser and scanners, the scanners each comprising mirrors, optics or a combination of mirrors and optics; predefining a lenticular volume to have a posterior face and an anterior face and edges that are connected via an annular edge face, the edge face having in projection along an optical axis of the eye a first ring width which is greater than a second ring width that would be created in the projection along the optical axis of the eye by a straight line extending perpendicularly from an edge of the posterior or the anterior face to the other of the posterior or the anterior face or to an imaginary continuation of the posterior face or the anterior face; and separating corneal tissue by applying focused laser radiation, wherein the control data control, during operation, the laser device including the laser and the scanners to emit the focused laser radiation into the cornea wherein a lenticular volume is isolated in the cornea and removal of the lenticular volume effects a desired correction of hyperopia.
 9. The method according to claim 8, further comprising: generating the control data such that the anterior face is positioned at a constant distance d_(F) from the anterior surface of the cornea and the posterior face is curved and has a radius of curvature R_(L)=R_(CV)*−d_(F), wherein R_(CV)* satisfies the following equation R _(CV)*=1/((1/R _(CV))+B _(BR)/((n _(c)−1)·(1−d _(HS) ·B _(BR))))+F, and R_(CV) is a radius of curvature of the cornea before removal of the lenticular volume, n_(c) is a refractive index of a material of the cornea, F is a correction factor, B_(BR) is a refractive power of a pair of spectacles suitable for correcting defective vision, and also d_(HS) is a distance at which the pair of spectacles having the refractive power B_(BR) would have to be positioned before a corneal apex in order to achieve a desired correction of defective vision by the pair of spectacles.
 10. The method according to claim 9, further comprising generating the control data such that the following applies F=(1−1/n _(c))·(d _(C) *−d _(C)), wherein d_(C) and d_(C)* respectively denote a thickness of the cornea before and after removal of the lenticular volume and the radius R_(CV)* can be calculated iteratively in that during each iteration step a change in thickness (d_(C)*−d_(C)) is concluded from the difference (R_(CV)*−R_(CV)) and the corresponding result obtained therefrom for the change in thickness is applied in the calculation of R_(CV)* in a next iteration step.
 11. The method according to claim 8, further comprising generating the control data such that the edge face has a first portion opening substantially perpendicularly into the anterior face and a second portion inclined more acutely toward the axis of vision.
 12. The method according to claim 11, further comprising generating the control data such that the first portion has a height d_(R) of more than 5 μm.
 13. The method according to claim 11, further comprising generating the control data such that the first portion has a height d_(R) of at least 10 μm.
 14. The method according to claim 11, further comprising generating the control data such that the second portion is positioned at an angle of from 80° to 100° relative to the direction of the axis of vision.
 15. A method for surgical correction of hyperopia in an eye, the method comprising: providing a laser device including a laser and scanners, the scanners each comprising mirrors, optics or a combination of mirrors and optics; separating corneal tissue and isolating and removing a lenticular volume from a cornea by applying laser radiation by application of the laser and the scanners, the removal of the lenticular volume from the cornea effecting a desired refractive correction wherein the lenticular volume has a posterior face and an anterior face, and edges that are connected via an annular edge face, the edge face having in projection along an optical axis of the eye a first ring width which is greater than a second ring width that would be created in the projection along the optical axis of the eye by a straight line extending perpendicularly from an edge of the posterior or the anterior face to the other of the posterior or the anterior face or to an imaginary continuation of the posterior face or the anterior face.
 16. The method according to claim 15, further comprising generating the lenticular volume such that the anterior face is positioned at a constant distance d_(F) from the anterior surface of the cornea and the posterior face is curved and has a radius of curvature R_(L)=R_(CV)*−d_(F), wherein R_(CV)* satisfies the following equation: R _(CV)*=1/((1/R _(CV))+B _(BR)/((n _(c)−1)·(1−d _(HS) ·B _(BR))))+F, and R_(CV) is a radius of curvature of the cornea before removal of the lenticular volume, n_(c) is a refractive index of a material of the cornea, F is a correction factor, B_(BR) is a refractive power of a pair of spectacles suitable for correcting defective vision, and also d_(HS) is a distance at which the pair of spectacles having the refractive power B_(BR) would have to be positioned before a corneal apex in order to achieve a desired correction of defective vision by the pair of spectacles.
 17. The method according to claim 16, further comprising generating the lenticular volume such that the following applies: F=(1−1/n _(c))·(d _(C) *−d _(C)), wherein d_(C) and d_(C)* respectively denote a thickness of the cornea before and after removal of the lenticular volume and the radius R_(CV)* can be calculated iteratively in that during each iteration step a change in thickness (d_(C)*−d_(C)) is concluded from the difference (R_(CV)*−R_(CV)) and the corresponding result obtained therefrom for the change in thickness is applied in the calculation of R_(CV)* in a next iteration step.
 18. The method according to claim 15, further comprising generating the lenticular volume such that the edge face has a first portion opening substantially perpendicularly into the anterior face and a second portion inclined more intensively toward the axis of vision.
 19. The method according to claim 18, further comprising generating the lenticular volume such that the first portion has a height d_(R) of more than 5 μm.
 20. The method according to claim 18, further comprising generating the lenticular volume such that the first portion has a height d_(R) of at least 10 μm.
 21. The method according to claim 18, further comprising generating the lenticular volume such that the second portion is positioned at an angle of from 80° to 100° relative to the direction of the axis of vision.
 22. The method according to claim 21, further comprising generating the lenticular volume such that the second portion is concave, based on the point at which the axis of vision passes through the front face of the cornea.
 23. The apparatus or the method according to claim 4, wherein the second portion is concave, based on the point at which the axis of vision passes through the front face of the cornea. 